US7194100B2 - Method for individualizing a hearing aid - Google Patents

Method for individualizing a hearing aid Download PDF

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Publication number
US7194100B2
US7194100B2 US09/829,700 US82970001A US7194100B2 US 7194100 B2 US7194100 B2 US 7194100B2 US 82970001 A US82970001 A US 82970001A US 7194100 B2 US7194100 B2 US 7194100B2
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Prior art keywords
loudness
factor
individual
weighted
hearing aid
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Expired - Fee Related, expires
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US09/829,700
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US20020146137A1 (en
Inventor
Volker Kühnel
Andreas Von Buol
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Sonova Holding AG
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Phonak AG
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Priority to US09/829,700 priority Critical patent/US7194100B2/en
Priority to CA002409838A priority patent/CA2409838A1/en
Priority to DE50102419T priority patent/DE50102419D1/de
Priority to PCT/CH2001/000232 priority patent/WO2001049068A2/de
Priority to DK01916843T priority patent/DK1290914T3/da
Priority to AU2001244029A priority patent/AU2001244029A1/en
Application filed by Phonak AG filed Critical Phonak AG
Priority to EP01916843A priority patent/EP1290914B1/de
Assigned to PHONAK AG reassignment PHONAK AG ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: VON BUOL, ANDREAS, KUHNEL, VOLKER
Publication of US20020146137A1 publication Critical patent/US20020146137A1/en
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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/35—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using translation techniques
    • H04R25/356—Amplitude, e.g. amplitude shift or compression
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting

Definitions

  • This invention relates to a method for individualizing a hearing aid.
  • Successfully fitting a hearing-impaired individual with a hearing aid that is to correct for the hearing impairment is a critical factor which, among other things, determines the person's acceptance of the hearing aid. In this context it is not only the nature and degree of the hearing impairment that is of significance but there are various other factors as well, for instance the person's particular perception of loudness levels.
  • EP-A2-0 661 905 describes one such method for fitting a person with a hearing aid. That earlier method addresses the correction of the damaged psycho-acoustic perception of an individual by a parameter adjustment in the hearing aid.
  • the targeted correction uses as a reference value the statistically determined average auditory perception of persons with normal hearing.
  • the loudness standard serving as a reference was established based on a group of persons with normal hearing, employing, where possible, the same procedure for determining that standard auditory function that is used in the specific individual measurements.
  • FIG. 1 is a schematic illustration of a quantification unit serving to quantify an individually perceived loudness level
  • FIG. 2 indicates the loudness level perceived by a person with normal hearing and, respectively, by a person with impaired hearing, as a function of volume and at a specific frequency;
  • FIG. 3 shows the loudness correction as a function of the loss of hearing (HVLS/LOHL function) of a hearing-impaired person
  • the invention provides the possibility of an individualized and consequently better adjustment of hearing aids by virtue of the fact that the hearing-aid setting takes into account deviations attributable to inaccurate measurements as well as scattered values resulting from different individual loudness perceptions, with appropriately weighted individually established parameters as well as the standard loudness perception contributing to the definition of optimal adaptation.
  • optimal adaptation in this case refers in particular to the setting of a balanced compression pattern and of the amplification, i.e. the frequency-dependent input/output characteristics of the hearing aid.
  • this is accomplished in particular by plotting the specific gradients of the individual scaling results as a function of the loss of hearing and approximating them by a specific LOHL function, i.e. by the gradient of the loudness factor as a function of the hearing loss HL.
  • the individual LOHL function when compared to the average hearing-impaired LOHL function permits the determination of a factor which describes the loudness sensitivity of the individual in comparison with the standard.
  • the individual HLL 0 factor compared to the average HLL 0 factor of the hearing-impaired, permits the determination of an offset which describes the mean value of the difference in the abscissa of the loudness function of the individual in comparison with the standard.
  • an audiogram is prepared. For a potential wearer of a hearing aid this is done by measuring the hearing thresholds for pure sounds at different frequencies. The increments of these audible limits are expressed and plotted as hearing loss in dB for each frequency and at certain frequency intervals. The audiogram thus allows for the determination of the auditory range in which there is a hearing loss. The audiogram also establishes data sampling points, meaning individual frequencies, at which loudness scaling is subsequently performed in the manner described next.
  • the loudness “L” is a psycho-acoustic variable which indicates how “loud” an acoustic signal is perceived by an individual.
  • the loudness does not necessarily match the physically transmitted energy of the signal.
  • a psycho-acoustic analysis of the impinging acoustic signal takes place in the ear within individual frequency bands, the so-called critical bands.
  • the loudness is determined by a band-specific processing of the signal and an inter-band superposition of the band-specific processing results, known as “loudness summation”.
  • loudness must be viewed as one of the most essential psycho-acoustic variables determining acoustic perception.
  • FIG. 1 One possibility to use the loudness individually perceived in response to selected acoustic signals as a variable for further processing is offered by the method schematically illustrated in FIG. 1 and described for instance by O. Heller in “Auditory Range Audiometry Employing the Categorization Method”, Psychological Articles 26, 1985, or by V. Hohmann in “Dynamics Compression for Hearing Aids, Psychoacoustical Fundamentals and Algorithms”, thesis at the Univ. of Göttingen ottingen, VDI-Verlag, Series 17, No.
  • a person I is exposed to an acoustic signal A which can be varied in a generator 1 in terms of its spectral composition and its transmitted sound pressure level.
  • the person I analyzes i.e. “categorizes” the acoustic signal A just heard by means of an input unit 3 within for instance eleven loudness steps or categories as illustrated in FIG. 1 . These steps are assigned numerical weights for instance from 0 to 10 categorical units (cu).
  • loudness scaling is performed at a minimum of one and preferably at three different frequencies or data sampling points.
  • the loudness L is expressed as function of the mean sound pressure level in dB-SPL for a sinusoidal signal of frequency f k .
  • the loudness L kN of the standard in the graph chosen increases in nonlinear fashion with the signal level; in a first approximation the slope for persons with normal hearing is expressed for all critical bands by the regression line indicated as N in FIG. 2 with a gradient ⁇ N in [categories per dB-SPL].
  • model parameter ⁇ N corresponds to a nonlinear amplification which for persons with normal hearing is approximately the same in each critical frequency band, whereas for hearing-impaired persons the determination must be made using ⁇ kI for each frequency or frequency band.
  • the straight line with the gradient ⁇ kI serves to approximate the nonlinear loudness function at frequency f k by means of a regression line.
  • L kI indicates the typical pattern of loudness L I of a hearing-impaired person at a frequency of f k .
  • a comparison of the curves L kN and L kI shows that the curve of a hearing-impaired person displays a greater offset (L o ) relative to zero and has a steeper slope than the standard curve.
  • the greater offset corresponds to a higher audible limit or hearing threshold; the phenomenon of the invariably steeper loudness curve is referred to as loudness “recruitment” or acquisition and reflects a higher ⁇ -parameter.
  • loudness scaling is performed at a minimum of one and preferably at three reference or data sampling points, i.e. at one or several different frequencies. Based on these reference values a so-called LOHL factor is established by plotting the gradients of the loudness factor a 1 , a 2 , a 3 . . . as a function of hearing loss HL in dB.
  • FIG. 3 shows an LOHL function for a hearing-impaired person, with the individual LOHL function, represented by the dashed line, established via three data sampling points for building a suitable model as explained below.
  • the individual LOHL factor illustrated in FIG. 3 shows less dispersion-related deviation than do the sampling points by themselves, thus providing a better reflection of changes in individual perception.
  • the targeted reference settings for the hearing aid already on the basis of this individual LOHL factor, to determine the gradient a at 0 dB hearing loss by extrapolation (dotted curve in FIG. 3 ) and to set the hearing aid accordingly, it has been found that the setting of the hearing aid can be substantially improved if data on the healthy ear are also included in the equation.
  • the normal loudness perception should be used as a reference for determining the individually needed compression at 0 dB hearing loss. In the process, according to the invention, the fact is taken into account that even the loudness perception of persons with normal hearing tends to vary to a more than negligible extent.
  • a mean value is established between the individual gradient ⁇ at 0 dB hearing loss, determined by measurements and by extrapolation, and the normal-loudness gradient, weighting the values based on their expected dispersion both for the individual gradient ⁇ at 0 dB hearing loss and for the normal-loudness gradient. Weighting the individual scaling data as a function of their respective quality and of the number of measuring points for the various scaling functions and the number of scaling operations themselves has proved to be useful.
  • a weighting of the individual gradient ⁇ at 0 dB hearing loss by a factor of 2 ⁇ 3 and a weighting of the normal-hearing gradient ⁇ N by a factor of 1 ⁇ 3 can lead to an exceedingly good adaptation of the hearing aid.
  • the abscissa section L 0 of the loudness factor in conjunction with the hearing loss information established in the audiogram permits the determination of an optimum band-specific amplification.
  • loudness scaling is performed at a minimum of one and preferably at three reference or data sampling points, i.e. at one or several different frequencies. Based on these data points the HLL 0 factor is established by plotting the abscissa sections for the loudness factor L 01 , L 02 , L 03 , . . . as a function of hearing loss HL in dB.
  • FIG. 4 shows the HLL 0 factor for a hearing-impaired person with the individual HLL 0 function, represented by the dashed line, established via three data sampling points for building a suitable model as explained below.
  • L 0 a L ⁇ HL+b L ⁇ log( HL )+ VP constL for 20 dB ⁇ HL ⁇ 100 dB, where
  • the HLL 0 factor illustrated in FIG. 4 shows less dispersion-related deviation than do the sampling points by themselves, thus providing a better reflection of changes in individual perception.
  • the targeted reference settings for the hearing aid already on the basis of this individual HLL 0 factor, to determine the level L 0 at 0 dB hearing loss by extrapolation (dotted curve in FIG. 3 ) and to set the hearing aid accordingly, it has been found that the setting of the hearing aid can be substantially improved if, similar to the gradient a, data on the healthy ear are also included in the equation.
  • the standard i.e.
  • normal loudness perception should be used as a reference for determining the individually needed compression at 0 dB hearing loss.
  • the fact is taken into account that even the loudness perception of persons with normal hearing tends to vary to a more than negligible extent.
  • a weighted mean value is established between the individual level L 0 at 0 dB hearing loss, determined by measurements and by extrapolation, and the normal level L 0 , weighting the values based on their expected dispersion both for the individual level L 0 at 0 dB hearing loss and for the normal level L 0 .
  • weighting the individual scaling data as a function of their respective quality and of the number of measuring points for the various scaling functions and the number of scaling operations themselves has proved to be useful.
  • a weighting of the individual level L 0 at 0 dB hearing loss by a factor of 1 ⁇ 3 and a weighting of the normal-level L 0 by a factor of 2 ⁇ 3 can lead to an exceedingly good adaptation of the hearing aid.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
  • Tone Control, Compression And Expansion, Limiting Amplitude (AREA)
US09/829,700 2001-04-10 2001-04-10 Method for individualizing a hearing aid Expired - Fee Related US7194100B2 (en)

Priority Applications (7)

Application Number Priority Date Filing Date Title
DE50102419T DE50102419D1 (de) 2001-04-10 2001-04-10 Verfahren zur anpassung eines hörgerätes an ein individuum
PCT/CH2001/000232 WO2001049068A2 (de) 2001-04-10 2001-04-10 Verfahren zur anpassung eines hörgerätes an ein individuum
DK01916843T DK1290914T3 (da) 2001-04-10 2001-04-10 Fremgangsmåde til tilpasning af et höreapparat til et individ
AU2001244029A AU2001244029A1 (en) 2001-04-10 2001-04-10 Method for adjustment of a hearing aid to suit an individual
US09/829,700 US7194100B2 (en) 2001-04-10 2001-04-10 Method for individualizing a hearing aid
EP01916843A EP1290914B1 (de) 2001-04-10 2001-04-10 Verfahren zur anpassung eines hörgerätes an ein individuum
CA002409838A CA2409838A1 (en) 2001-04-10 2001-04-10 Method for adjustment of a hearing aid to suit an individual

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
PCT/CH2001/000232 WO2001049068A2 (de) 2001-04-10 2001-04-10 Verfahren zur anpassung eines hörgerätes an ein individuum
US09/829,700 US7194100B2 (en) 2001-04-10 2001-04-10 Method for individualizing a hearing aid

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US20020146137A1 US20020146137A1 (en) 2002-10-10
US7194100B2 true US7194100B2 (en) 2007-03-20

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US (1) US7194100B2 (de)
EP (1) EP1290914B1 (de)
AU (1) AU2001244029A1 (de)
CA (1) CA2409838A1 (de)
DE (1) DE50102419D1 (de)
DK (1) DK1290914T3 (de)
WO (1) WO2001049068A2 (de)

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20050226427A1 (en) * 2003-08-20 2005-10-13 Adam Hersbach Audio amplification apparatus
US20070098187A1 (en) * 2005-11-01 2007-05-03 Samsung Electronics Co., Ltd. Method and apparatus for reproducing music file
US20090028362A1 (en) * 2007-07-27 2009-01-29 Matthias Frohlich Hearing device with a visualized psychoacoustic variable and corresponding method
US20090264793A1 (en) * 2008-04-17 2009-10-22 Siemens Medical Instruments Pte. Ltd. Method for determining a time constant of the hearing and method for adjusting a hearing apparatus
US20100278356A1 (en) * 2004-04-01 2010-11-04 Phonak Ag Audio amplification apparatus
US20120059274A1 (en) * 2002-01-30 2012-03-08 Natus Medical Incorporated Method for automatic non-cooperative frequency specific assessment of hearing impairment and fitting of hearing aids

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US7020581B2 (en) * 2002-10-18 2006-03-28 Medacoustics Research & Technology Medical hearing aid analysis system
KR101164937B1 (ko) * 2003-05-28 2012-07-12 돌비 레버러토리즈 라이쎈싱 코오포레이션 오디오 신호의 인식된 라우드니스를 계산 및 조정하는방법, 장치 및 컴퓨터 프로그램
US7435228B2 (en) * 2003-07-18 2008-10-14 Harris Corporation High fidelity hearing restoration
CN101048935B (zh) 2004-10-26 2011-03-23 杜比实验室特许公司 控制音频信号的单位响度或部分单位响度的方法和设备
US8199933B2 (en) 2004-10-26 2012-06-12 Dolby Laboratories Licensing Corporation Calculating and adjusting the perceived loudness and/or the perceived spectral balance of an audio signal
BRPI0610719B1 (pt) * 2005-04-18 2015-11-24 Basf Ag preparação, processo para a produção da mesma, e, uso de preparações
US7890377B2 (en) * 2005-10-31 2011-02-15 Phonak Ag Method for producing an order and ordering apparatus
TWI517562B (zh) 2006-04-04 2016-01-11 杜比實驗室特許公司 用於將多聲道音訊信號之全面感知響度縮放一期望量的方法、裝置及電腦程式
JP5185254B2 (ja) * 2006-04-04 2013-04-17 ドルビー ラボラトリーズ ライセンシング コーポレイション Ｍｄｃｔ領域におけるオーディオ信号音量測定と改良
AU2007243586B2 (en) 2006-04-27 2010-12-23 Dolby Laboratories Licensing Corporation Audio gain control using specific-loudness-based auditory event detection
WO2008051347A2 (en) 2006-10-20 2008-05-02 Dolby Laboratories Licensing Corporation Audio dynamics processing using a reset
US8521314B2 (en) * 2006-11-01 2013-08-27 Dolby Laboratories Licensing Corporation Hierarchical control path with constraints for audio dynamics processing
CN101790758B (zh) * 2007-07-13 2013-01-09 杜比实验室特许公司 用于控制音频信号的信号处理的设备和方法
DE102007035174B4 (de) 2007-07-27 2014-12-04 Siemens Medical Instruments Pte. Ltd. Hörvorrichtung gesteuert durch ein perzeptives Modell und entsprechendes Verfahren
CN102017402B (zh) 2007-12-21 2015-01-07 Dts有限责任公司 用于调节音频信号的感知响度的系统
US8144909B2 (en) 2008-08-12 2012-03-27 Cochlear Limited Customization of bone conduction hearing devices
US8538042B2 (en) 2009-08-11 2013-09-17 Dts Llc System for increasing perceived loudness of speakers
US9172345B2 (en) * 2010-07-27 2015-10-27 Bitwave Pte Ltd Personalized adjustment of an audio device
US9479879B2 (en) 2011-03-23 2016-10-25 Cochlear Limited Fitting of hearing devices
US9312829B2 (en) 2012-04-12 2016-04-12 Dts Llc System for adjusting loudness of audio signals in real time

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USRE34961E (en) * 1988-05-10 1995-06-06 The Minnesota Mining And Manufacturing Company Method and apparatus for determining acoustic parameters of an auditory prosthesis using software model
US5729658A (en) 1994-06-17 1998-03-17 Massachusetts Eye And Ear Infirmary Evaluating intelligibility of speech reproduction and transmission across multiple listening conditions
EP0661905A2 (de) 1995-03-13 1995-07-05 Phonak Ag Verfahren zur Anpassung eines Hörgerätes, Vorrichtung hierzu und Hörgerät
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Cited By (12)

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Publication number Priority date Publication date Assignee Title
US20120059274A1 (en) * 2002-01-30 2012-03-08 Natus Medical Incorporated Method for automatic non-cooperative frequency specific assessment of hearing impairment and fitting of hearing aids
US8277390B2 (en) * 2002-01-30 2012-10-02 Natus Medical Incorporated Method for automatic non-cooperative frequency specific assessment of hearing impairment and fitting of hearing aids
US20050226427A1 (en) * 2003-08-20 2005-10-13 Adam Hersbach Audio amplification apparatus
US7756276B2 (en) * 2003-08-20 2010-07-13 Phonak Ag Audio amplification apparatus
US20100278356A1 (en) * 2004-04-01 2010-11-04 Phonak Ag Audio amplification apparatus
US8351626B2 (en) 2004-04-01 2013-01-08 Phonak Ag Audio amplification apparatus
US20070098187A1 (en) * 2005-11-01 2007-05-03 Samsung Electronics Co., Ltd. Method and apparatus for reproducing music file
US8031884B2 (en) * 2005-11-01 2011-10-04 Samsung Electronics Co., Ltd Method and apparatus for reproducing music file
US20090028362A1 (en) * 2007-07-27 2009-01-29 Matthias Frohlich Hearing device with a visualized psychoacoustic variable and corresponding method
US8213650B2 (en) * 2007-07-27 2012-07-03 Siemens Medical Instruments Pte. Ltd. Hearing device with a visualized psychoacoustic variable and corresponding method
US20090264793A1 (en) * 2008-04-17 2009-10-22 Siemens Medical Instruments Pte. Ltd. Method for determining a time constant of the hearing and method for adjusting a hearing apparatus
US8238591B2 (en) * 2008-04-17 2012-08-07 Siemens Medical Instruments Pte. Ltd. Method for determining a time constant of the hearing and method for adjusting a hearing apparatus

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US20020146137A1 (en) 2002-10-10
EP1290914A2 (de) 2003-03-12
WO2001049068A3 (de) 2002-09-12
AU2001244029A1 (en) 2001-07-09
DK1290914T3 (da) 2004-09-27
EP1290914B1 (de) 2004-05-26
DE50102419D1 (de) 2004-07-01
CA2409838A1 (en) 2002-11-19
WO2001049068A2 (de) 2001-07-05

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